Current split circuit for equally splitting current between parallel connected led luminaire strings

ABSTRACT

A system and method for equally splitting the current supplied to parallel connected strings of LEDs. The system and method includes a current splitting circuit such as a mirror circuit that divides the current substantially equally between two or more parallel connected strings of LEDs. The current splitting circuit ensures that illumination levels of the strings of LEDs are uniform without requiring the strings of LEDs to be binned. The current splitting circuit also allows the strings of LEDs to be dimmed in both pulse width modulation (PWM) and continuous modes.

BACKGROUND TO THE INVENTION

The present application relates to the field of radiograph CT, and moreparticularly, to a CT collimator having a single motor drive system anda radiograph CT system having the CT collimator.

At present, radiograph CT systems such as X-ray CT system are widelyused in various medical institutions for three-dimensional imaging ofthe regions of interest of the subjects to assist the clinicians toachieve an accurate medical diagnosis of the subjects.

In a radiograph CT system, a radiation tube generating cone-shapedradiation beams and a detector detecting the radiation beams rotatearound a rotation center, wherein the detector is disposed opposite tothe radiation tube and consists of detector elements arranged in amatrix form. Projection data generated by the radiation beamstransmitting through the subject are collected; based on the collectedprojection data, an image of the region of interest of the subject isreconstructed; and then the reconstructed CT image is displayed on animage display device.

In a radiograph CT system, a collimator is generally provided betweenthe radiation tube and the subject to be detected. By adjusting a widthof the aperture of the collimator, the width of the radiation beams in adirection parallel to the subject is controlled so as to control athickness of the scan.

A conventional collimator generally has at least two different motordrive systems to meet the requirements of multi-slot opening and Z-beamtracking Such a collimator comprises at least two gates or cams, whichare driven by at least two different motor drive systems, and hence havehigher cost.

Some newly developed collimators use a single motor drive system to meetthe requirements of slot opening and Z-beam tracking For example, arecently developed collimator comprises a plate having a plurality ofslots driven by a single motor drive system. Each slot corresponds to acollimator aperture of a different width. Though using a single motordrive system in place of the conventional two drive systems to reducethe cost of the drive system, such a collimator requires converting therotational motion of the motor into a linear motion and hence the needof such components as lead screw and rails. Therefore, there is a needfor a CT collimator and a CT system that, in case of a focus shift ofthe radiation source due to temperature changes during a CT scan, canautomatically correct the position of the collimator aperture and enablethe radiation beams to be irradiated to the subject via the collimatordirectly in a rotational movement manner without departing from thepredetermined region of interest so that the detection area of theradiation beams projected to the detector after passing through thesubject remains unchanged.

SUMMARY OF THE INVENTION

Embodiments of the present invention provide a CT collimator and a CTsystem comprising the CT collimator capable of solving the aboveproblems.

According to a first aspect of the present invention, there is provideda CT collimator. The CT collimator comprises a rotating slot partdisposed on a rotation shaft and having a plurality of blades, whereineach blade has a slot of a different width and a radiation beam enteringthe collimator can only pass via a slot in one of the plurality ofblades, wherein an edge of each blade slot along a longitudinaldirection of this blade has a convex curved surface structure, and in avertical plane along a longitudinal direction of each blade slot, thetwo side edges of the slot are curved, and wherein each blade isarranged to be eccentric to the center of the rotation shaft.

The CT collimator according to an embodiment of the present inventionfurther comprises a single motor configured to drive the rotating slotpart to rotate around the rotation shaft; and an encoder for monitoringan angle of rotation of the rotating slot part around the center of therotation shaft.

The CT collimator according to an embodiment of the present inventionfurther comprises a single motor configured to drive the rotating slotpart to rotate around the rotation shaft, wherein the single motor isprovided with an encoder for monitoring an angle of rotation of therotating slot part around the center of the rotation shaft.

In the CT collimator according to an embodiment of the presentinvention, the curved surface structure of each blade edge comprises twocurved lines in a vertical plane along the longitudinal direction ofthis blade, and a blade slot of this blade allows radiation beamsbetween radiation lines tangent to the two curved lines to pass through.

In the CT collimator according to the an embodiment of the presentinvention, the curved surface structure of each blade edge comprises twocircular arcs in a vertical plane along the longitudinal direction ofthis blade, and a blade slot of this blade allows radiation beamsbetween radiation lines tangent to the two circular arcs to passthrough.

In the CT collimator according to an embodiment of the presentinvention, two circles for the two circular arcs are respectively: when,in the vertical plane, the rotation of a first connecting line and asecond connecting line between a maximum shift position to the left of aradiation source and left and right edge points of a radiation detectionarea of a radiation detector around the center of the rotation shaftrelative to a third connecting line and a fourth connecting line betweena maximum shift position to the right of the radiation source and theleft and right edge points of the radiation detection area reaches aposition where there are respective intersections in a blade thicknessregion between the first connecting line and the third connecting lineand between the second connecting line and the fourth connecting line, afirst circle that is tangent to the first connecting line and the thirdconnecting line at said position, and a second circle that is tangent tothe second connecting line and the fourth connecting line at saidposition.

In the CT collimator according to an embodiment of the presentinvention, each blade has a planar structure, and a width of a slot ofeach blade gradually increases from the center of the slot to the twoends along the longitudinal direction of the blade.

In the CT collimator according to an embodiment of the presentinvention, when each blade has an arc structure whose center of circleis on a focal point of a radiation source outside the collimator whenthis blade is located in the horizontal position.

In the CT collimator according to an embodiment of the presentinvention, when the center of the rotation shaft is not located in anextended region of each blade slot along the thickness direction of theblade, said blade is eccentric to the center of the rotation shaft.

According to an embodiment of the present invention, there is provided aCT system. The CT system comprises a CT collimator according to thefirst aspect of the present invention, a radiation detection areamonitoring unit disposed on a radiation detector, and a collimatorcontroller that selects one of a plurality of blades of the rotatingslot part according to a region of interest of a subject to allow adesired radiation beam to be projected to the region of interest of thesubject, wherein the radiation detection area monitoring unit monitors,during a CT scan, an offset of the radiation detection area on theradiation detector caused by focus shift of the radiation source asradiation beam is projected to the radiation detector via the selectedblade of the CT collimator, and wherein the collimator controller isconfigured to correct an angle of rotation of the rotating slot part ofthe CT collimator according to the monitored offset received from theradiation detection area monitoring unit to eliminate the offset of theradiation detection area caused by the focus shift of the radiationsource for performing Z-beam tracking

The CT system according to an embodiment of the present invention is anX-ray CT system.

In the CT system according to an embodiment of the present invention,the collimator controller comprises a memory or is coupled to a memory.

In the CT system according to an embodiment of the present invention, aplurality of offsets of the radiation detection area predetermined foreach blade in the rotating slot part and a plurality of correspondingcorrection angles that the rotating slot part is required to rotate forperforming Z-beam tracking are stored in the form of a table in thememory.

In the CT system according to an embodiment of the present invention,the collimator controller is configured to: determine a rotationcorrection angle of the rotating slot part for the selected bladethrough a search in said table in said memory according to the monitoredoffset of the radiation detection area, and perform Z-beam trackingaccording to the determined rotation correction angle of the rotatingslot part and the current angle of the selected blade.

In the CT system according to an embodiment of the present invention,the collimator controller is configured to: in case of failure to find acorresponding rotation correction angle of the rotating slot part insaid table according to the monitored offset of the radiation detectionarea, search for two rotation correction angles corresponding to twooffsets close to the monitored offset of the radiation detection area,and use an average of the two rotation correction angles or aninterpolation therebetween as the determined rotation correction angleof the rotating slot part; or in case of failure to find a correspondingrotation correction angle of the rotating slot part in said tableaccording to the monitored offset of the radiation detection area,search for a rotation correction angle corresponding to the shiftclosest to the monitored offset of the radiation detection area and useit as the determined rotation correction angle of the rotating slotpart.

In the CT system according to an embodiment of the present invention, aplurality of focus shifts of the radiation source predetermined for eachblade in the rotating slot part and a plurality of rotation correctionangles of the rotating slot part required for Z-beam tracking are storedin the form of a table in the memory.

In the CT system according to an embodiment of the present invention,the collimator controller is configured to: determine a focus shift ofthe radiation source according to the monitored offset of the radiationdetection area, determine a rotation correction angle of the rotatingslot part for the selected blade through a search in said table in saidmemory according to the determined focus shift, and perform Z-beamtracking according to the determined rotation correction angle of therotating slot part and the current angle of the selected blade.

In the CT system according to an embodiment of the present invention,the collimator controller is configured to: in case of failure to find acorresponding rotation correction angle of the rotating slot part insaid table according to the determined focus shift, search for tworotation correction angles corresponding to two focus shifts close tothe determined focus shift, and use an average of the two rotationcorrection angles or an interpolation therebetween as the determinedrotation correction angle of the rotating slot part; or in case offailure to find a corresponding rotation correction angle of therotating slot part in said table according to the determined focusshift, search for a rotation correction angle corresponding to the focusshift closest to the determined focus shift and use it as the determinedrotation correction angle of the rotating slot part.

In the CT system according to an embodiment of the present invention,the collimator controller is further configured to, after correction ofa rotation angle of the rotating slot part of the CT collimator, comparea latest monitored offset of the radiation detection area received fromthe radiation detection area monitoring unit with a predeterminedthreshold, and if the latest monitored offset of the radiation detectionarea does not exceed the predetermined threshold, then stop the Z-beamtracking; or if the latest monitored offset of the radiation detectionarea exceeds the predetermined threshold, then perform a new Z-beamtracking until the latest monitored offset of the radiation detectionarea does not exceed the predetermined threshold.

In the CT collimator and CT system comprising said CT collimatoraccording to embodiments of the present invention, a plurality of bladeshaving variable slot widths can be provided in the CT collimatoraccording to the needs of a CT scan. An edge of each blade slot along alongitudinal direction of the blade has a convex curved surfacestructure (namely, in a vertical plane along a longitudinal direction ofthe blade slot, the two side edges of the slot are curved) so that whena focus shift of the radiation source along a focus shift path occurs asa result of temperature change, by rotating the selected blade about therotation center eccentric to the blade a correction angle correspondingto the focus shift, the radiation beams reaching the radiation detectorvia the blade slot are maintained at the same region as the circumstancewhere focus shift does not occur. Therefore, the CT collimator and CTsystem according to an embodiment of the present invention eliminate theneed to relocate other components such as the radiation detector or thesubject when a focus shift of the radiation source occurs.

BRIEF DESCRIPTION OF THE DRAWINGS

In the following some exemplary embodiments of the present inventionwill be described in detail with reference to the accompanying drawings,in which like or similar elements are denoted by the same referencenumerals, wherein:

FIGS. 1A and 1B show a radiograph CT system according to an exemplaryembodiment of the present invention;

FIG. 2 shows a CT collimator according to an exemplary embodiment of thepresent invention;

FIGS. 3A, 3B, 3C, and 3D show an aperture assembly in a CT collimatoraccording to an exemplary embodiment of the present invention;

FIGS. 4A, 4B, 4C, and 4D illustrate a method for determining an innercircular arc and an outer circular arc of a blade slot in an apertureassembly in a CT collimator according to an exemplary embodiment of thepresent invention;

FIG. 5 shows an offset of the X-ray detection area on the X-ray detectorwhen focus shift of the X-ray tube occurs and no Z-beam tracking isemployed in the collimator; and

FIGS. 6A, 6B, 6C, and 6D show Z-beam tracking according to an exemplaryembodiment of the present invention.

DETAILED DESCRIPTION OF THE INVENTION

In the following detailed description, exemplary embodiments of thepresent invention are described with reference to the accompanyingdrawings. However, it will be appreciated by persons skilled in the artthat the present invention is not limited to these exemplaryembodiments.

FIGS. 1A and 1B show a radiograph CT system 100 according to anexemplary embodiment of the present invention. In an embodiment, theradiograph CT system 100 is an X-ray CT system.

As shown in FIGS. 1A and 1B, the X-ray CT system 100 mainly includesthree parts: a scan gantry 110, a support table 116 for positioning asubject 114 to be detected, and an operation console 130. The scangantry 110 includes an X-ray tube 102. X-rays 106 emitted from the X-raytube 102 pass through a collimator 104 to form an X-ray beam of suchshapes as fan shaped beam and cone shaped beam, to be irradiated to aregion of interest of the subject 114. The X-ray beam that passesthrough the subject 114 is applied to an X-ray detector 112 disposed onthe other side of the subject 114. The X-ray detector 112 has aplurality of two-dimensional X-ray detecting elements in the propagationdirection (the signal channel direction) and the thickness Z direction(column direction) of the fan-shaped X-ray beam.

A data acquisition system (DAS) 124 is coupled to the X-ray detector112. The data acquisition system 124 collects the data detected by eachof the X-ray detecting elements of the X-ray detector 124 for using asthe projection data. The X-ray radiation from the X-ray tube 102 iscontrolled by an X-ray controller 122. In FIG. 1B, the connectionsbetween the X-ray tube 102 and the X-ray controller 122 are not shown.

The data acquisition system 124 collects data related to the tubevoltage and tube current applied to the X-ray tube 102 by the X-raycontroller 122. In FIG. 1B, the connections between the X-ray controller122 and the data acquisition system 124 are omitted.

The collimator 104 is controlled by a collimator controller 120. In anembodiment, the collimator 104 and the collimator controller 120 are twoseparate components. In an embodiment, the collimator controller 120 maybe disposed within the collimator 104. In FIG. 1B, the connectionsbetween the collimator 104 and the collimator controller 120 are omitted

Components like the X-ray tube 102, the collimator 104, the X-raydetector 112, the data acquisition system 124, the X-ray controller 122and the collimator controller 120 are mounted in a rotating portion 128of the scan gantry 110. The rotating portion 128 rotates under thecontrol of a rotation controller 126. In FIG. 1B, the connectionsbetween the rotating portion 128 and the rotation controller 126 are notshown.

Under the action of a drive system such as a motor, the support table116 can be moved together with the subject 114 carried thereon along alongitudinal axis 118 of the subject into an opening 108 of the scangantry 110, so that the region of interest of the subject 114 issubstantially perpendicular to the X-ray beam irradiated thereon throughthe collimator 104.

The operation console 130 has a central processor 136 such as acomputer. A control interface 140 is connected to the central processor136. The scan gantry 110 and the support table 116 are connected to thecontrol interface 140. The central processor 136 controls the scangantry 110 and the support table 116 via the control interface 140.

The data acquisition system 124, the X-ray controller 122, thecollimator controller 120 and the rotation controller 126 in the scangantry 110 are controlled via the control interface 140. In FIG. 1B theseparate connections between the relevant parts and the controlinterface 140 are not shown.

A data acquisition buffer 138 is connected to the central processor 136.The data acquisition system 124 of the scan gantry 110 is connected tothe data acquisition buffer 138. Projection data collected by the dataacquisition system 124 are inputted to the central processor 136 via thedata acquisition buffer 138.

The central processor 136 uses the projection data inputted from thedata acquisition buffer 138 to perform an image reconstruction. Inperforming image reconstruction, such methods as the filtered backprojection method, and three-dimensional image reconstruction method canbe used. A storage device 142 is connected to the central processor 136.The storage device 142 may be used to store data, reconstructed imagesand procedures for implementing the various functions of the X-ray CTsystem 100.

A display device 132 and an input device 134 are connected to thecentral processor 136, respectively. The display device 132 displays thereconstructed images and other information output from the centralprocessor 136. An operator can input various instructions and parametersto the central processor 136 via the input device 134. Through thedisplay device 132 and the input device 134, the operator can achieve aninteractive operation of the X-ray CT system 100.

FIG. 2 shows a schematic structural diagram of a radiograph CTcollimator 104 according to an exemplary embodiment of the presentinvention. As shown in FIG. 2, the collimator 104 includes four mainparts: a collimator case 203, a collimator cover 202, a filter assembly201 and an aperture assembly 204. The aperture assembly 204 selectsblades of different slot widths to allow the desired X-ray beam to reachthe X-ray detector 112. The filter assembly 201 filters the X-ray beamsfrom the X-ray tube 104 to eliminate the scattered X-ray beams. Thecollimator case 203 is used for supporting, fixing and housing variouscomponents of the collimator 104. The collimator cover 202 providesshielding for the collimator 104.

FIGS. 3A, 3B, 3C, and 3D show an exemplary structure of the apertureassembly 204 shown in FIG. 2. As shown in FIG. 3A, the aperture assembly204 mainly includes three parts: a rotating slot part 2041, a singlemotor drive system 2043 driving the rotation of the rotating slot part2041, and an encoder 2042 detecting the rotation angle of the rotatingslot part 2041. In an embodiment, the motor drive system 2043 and theencoder 2042 are two separate parts. In an embodiment, the encoder 2042may be disposed within the motor drive system 2043. The rotating slotpart 2041 and the encoder 2042 can rotate together when driven by themotor drive system 2043.

Since the rotating slot part 2041 is directly driven by the motor drivesystem 2043, no rails, ball screw or lead screw are needed to convertthe rotational motion into a linear motion, thereby simplifying themechanical structure of the drive system of the collimator 104.

FIG. 3B shows an exemplary structure of the rotating slot part 2041shown in FIG. 3A, and provides a cross-sectional view of the rotatingslot part 2041 in a direction perpendicular to a longitudinal directionof the rotating slot part. As shown in FIG. 3B, the rotating slot part2041 includes a rotation shaft 2044 and a plurality of blades 2045 fixedto the rotation shaft 2044 and rotating together with the rotation shaft2044. Each blade has a slot of a different width and is provided with ashielding material to block the undesired X-ray beam entering thecollimator 104, so that the X-ray beam can only pass via the slot in theblade for being irradiated to the region of interest of the subject 114.

The rotating slot part 2041 as shown in FIG. 3B has four blades andtherefore four different slot widths. The four blades may be disposedaround the rotation shaft 2044 in an evenly spaced or unevenly spacedmanner. The number of blades on the rotating slot part 2041 can bedetermined according to actual needs, and can be set to, for example, 2,3, 4, 5, etc.

In an embodiment, each blade has a planar structure, and as shown inFIG. 3C, the width of the slot of each blade gradually increases fromthe center of the slot to the two ends along the longitudinal directionof the blade. In an embodiment, each blade and the blade slot have anarc structure whose center of circle, like the arc structure of theX-ray detector 112 disposed on the other side of the subject 114, is onthe focal point of the X-ray tube 102.

The two edges of each blade slot has a convex curved surface structurealong the longitudinal direction of the blade. As shown in FIG. 3D, theedges of the slot of each blade 2045 has a curved shape in the crosssectional view along a thickness direction perpendicular to thelongitudinal direction of the blade. Each blade is disposed to beeccentric to the rotation center of the rotating slot part 2041, so thatthe blade rotation center is not in an extended region of the slot alongthe thickness direction of the blade. As described below, by configuringthe edges of each blade blot as having a convex curved surfacestructure, and allowing each blade to be eccentric to the rotationcenter of the rotating slot part 2041, it is possible to maintain theX-ray detection area on the X-ray detector 112 unchanged throughadjustment of the rotating angle of the blade when the focus of theX-ray tube 102 shifts.

When carrying on a CT examination on the subject 114, the operatorselects a slot width of the aperture assembly 204 of the collimator 104via the input device 134. A control command is sent from the centralprocessor 136 to the collimator controller 120. Under the action of thecollimator controller 120, the motor drive system 2043 causes the bladeof the rotating slot part 2041 having the desired slot width to rotateto a substantially horizontal position so that said blade issubstantially perpendicular to the central X-ray beam emitted from theX-ray tube. Thus, X-ray beams entering the collimator 104 can only beirradiated to the region of interest of the subject 114 through the slotof said blade and pass through the subject 114 for being projected tothe X-ray detector 112, thereby forming an X-ray detection area.

During operation, the focus of the X-ray tube 102 will shift as the tubetemperature changes. Where the position of the selected blade of thecollimator 104 remains unchanged, as compared with the circumstancewhere no focus shift takes places, a corresponding shift will occur tothe X-ray beam irradiated to the subject 114 via the blade slot, whicheventually results in a relatively large offset of the X-ray detectionarea on the X-ray detector 112.

As shown in FIG. 5, in case of no focus shift of the X-ray tube 102during a CT scan, the X-ray detection area between the left edge D1 andthe right edge D2 of the X-ray beam projected to the X-ray detector 112via the slot of the selected blade of the collimator 104 is representedby A1. When the focus of the X-ray tube shifts due to temperature changeduring a CT scan along a focus shift path to the left edge of the focusshift path, the change of the X-ray detection area for the X-ray beamprojected to the X-ray detector 112 via the slot of the selected bladeis represented by A4. As shown, the right edge of the X-ray detectionarea of the X-ray detector 112 offsets from point D2 to point D4.Similarly, when due to temperature change the focus of the X-ray tube102 shifts along a focus shift path to the right edge of the focus shiftpath, the change of the X-ray detection area for the X-ray beamprojected to the X-ray detector via the blade slot is represented by A5.As shown, the left edge of the X-ray detection area of the X-raydetector 112 offsets from point D1 to point D3. Therefore, when focusshift occurs to the X-ray tube 102, if the position of the selectedblade of the collimator 104 is not corrected, namely, not to performZ-beam tracking, then the detection area for the X-ray beam projected tothe X-ray detector 112 via the selected blade of the collimator 104 willdeviate from the X-ray detection area A1 when focus shift does not occurto the X-ray tube 102.

In an embodiment, the curved lines of the curved surface structure ofeach blade slot edge in the cross-sectional view along a thicknessdirection perpendicular to the longitudinal direction of the blade asshown in FIG. 3D are circular arcs, wherein the circular arc close tothe rotation center of the blade is referred to as an inner circulararc, and the circular arc away from the rotation center of the blade isreferred to as an outer circular arc.

In the following, embodiments of the present invention will be furtherexplained by taking the example where the curved lines of the curvedsurface structure of each blade slot edge in a vertical plane along thelongitudinal direction of the blade slot are circular arcs. The skilledperson will appreciate that the curved lines of the curved surfacestructure of each blade slot edge in a vertical plane along thelongitudinal direction of the blade slot may be elliptical arcs or anyother curved lines.

In an embodiment, an unequal angle tracking method as described belowwith reference to FIGS. 4A, 4B, 4C, and 4D can be used to determine theinner and outer circular arcs of the blade slot. For convenience ofexplanation, a cross-sectional view of the blade slot center along athickness direction perpendicular to the longitudinal direction of theblade is used as an example for illustration.

FIG. 4A shows exemplary focus positions FP1-FP5 of the X-ray tube 102and edge lines L1-L10 of the X-ray beam when the X-ray beam emitted fromthe X-ray tube 102 at these focus positions is projected to the X-raydetector 112 via the blade slot, wherein focus positions FP1 and PF5represent the largest shifts of the focus of the X-ray tube 102 alongthe focus shift path. The focus shift path and range of the X-ray tubeare determined by its structure and size.

As shown in FIG. 4A, when the focus of the X-ray tube 102 is at FP1, theblade slot allows X-ray beams between lines L1 and L6 to pass through;when the focus of the X-ray tube is at FP2, the blade slot allows X-raybeams between lines L2 and L7 to pass through, and in the same manner,when the focus of the X-ray tube is at FP5, the blade slot allows X-raybeams between lines L5 and L10 to pass through.

The width of the blade slot and the positions of the inner and outercircular arcs thereof can be determined based on the requirement on thewidth of the X-ray detection area of the X-ray detector 112 during theCT scan, as well as the position and size of the various components ofthe CT system.

Specifically, as shown in FIG. 4B, a two-dimensional coordinate systemYOZ is established using the rotation center O of the blade as thecenter of coordinate, wherein the horizontal line of the rotation centerO is the OZ axis of the two-dimensional coordinate system. In theestablished two-dimensional coordinate system YOZ, the X-ray detectionarea of the X-ray detector 112 (namely, the edge points D1 and D2 of theX-ray detection area as shown in FIG. 6A), the position of the bladeslot, the focus position of the X-ray tube 102 and the maximum shiftposition are known. Therefore, it is possible to determine, when thefocus of the X-ray tube 102 is at the right maximum shift position FP5,the position of the X-ray line L10 that arrives at the left edge pointD1 (see FIG. 6A) of the X-ray detection area of the X-ray detector 112via the left edge point of the blade slot, and the position of the X-rayline L5 that arrives at the right edge point D2 (see FIG. 6A) of theX-ray detection area of the X-ray detector 112 via the right edge pointof the blade slot in the two-dimensional coordinate system YOZ, and itis also possible to determine, when the focus of the X-ray tube 102 isat the left maximum shift position FP1, the position of the X-ray lineL6 that arrives at the left edge point D1 of the X-ray detection area ofthe X-ray detector 112 via the left edge point of the blade slot, andthe position of the X-ray line L1 that arrives at the right edge pointD2 of the X-ray detection area of the X-ray detector 112 via the rightedge point of the blade slot in the two-dimensional coordinate systemYOZ.

Still referring to FIG. 4B, maintain the positions of the X-ray linesL10 and L5 transmitted via the left and right edge points of the bladeslot when the focus of the X-ray tube 102 is at the right maximum shiftposition FP5 unchanged and maintain the blade in a horizontal position,rotate the X-ray lines L6 and L1 transmitted via the left and right edgepoints of the blade slot when the focus of the X-ray tube 102 is at theleft maximum shift position FP1 an angle of B around the blade rotationcenter O to enable lines L6 and L10 to have an intersection in theregion along the thickness direction of the blade and to enable lines L1and L5 to also have an intersection in the same region, as shown in FIG.4C. If, during the rotation of the lines L6 and L1 around the bladerotation center O, the intersection of the lines L6 and L10 and theintersection of the lines L1 and L5 are not in the region along thethickness direction of the blade, then the thickness of the blade andthe eccentricity between the blade slot and the rotation center O can beadjusted until the intersection of the lines L6 and L10 and theintersection of the lines L1 and L5 are in the region along thethickness direction of the blade, as the lines L6 and L1 rotate aroundthe blade rotation center O.

Thereafter, as shown in FIG. 4D, a predetermined radius Ro is used toset an outer circular arc near the intersection of lines L6 and L10 asdescribed above, wherein the circle where the outer circular arc residesis tangent to the X-ray lines L6 and L10; similarly, a predeterminedradius Rn is used to set an inner circular arc near the intersection oflines L1 and L5, wherein the circle where the inner circular arc residesis tangent to the X-ray lines L1 and L5, and wherein the width of theblade slot is determined by the inner and outer circular arcs as setabove. The radii Ro and Rn of the outer and inner circular arcs may beset according to, for example, the requirement on the curvature of theouter and inner circular arcs. The radii Ro and Rn of the outer andinner circular arcs are appropriately selected so that the diameters ofthe circles where the outer and inner circular arcs reside are not lessthan the blade thickness. Besides, when relatively large values areselected for Ro and Rn, the outer and inner circular arcs should have anappropriate curvature so that the edges of the blade slot along thelongitudinal direction have a convex curved surface structure.

In an embodiment, an equal angle tracking method similar to theabove-described unequal angle tracking method or other similar methodsmay be used to determine the curved lines of the curved surfacestructure of each blade slot edge in a vertical plane along thelongitudinal direction of the blade slot.

In an embodiment, after determining the shape of the curved surfacestructure of the edge of each blade slot edge in a vertical plane alongthe longitudinal direction of the blade slot, such as the inner andouter curved lines of the inner and outer circular arcs, the inner andouter curved lines are extended from the center position to the two endsof the slot in accordance with the shape of the slot edge, to enable theedges of the blade slot along the longitudinal direction to have convexcurved surface structures, so that the X-rays projected on the X-raydetector 112 will have equal width in the Z direction. In an embodiment,the blade and the slot thereof may be divided into several slotsegments, and the above-described unequal angle tracking method or equalangle tracking method is used to determine for each slot segment, theshape of the inner and outer curved lines (such as the inner and outercircular arcs) of the slot segment in the vertical plane along thelongitudinal direction of the blade slot. Then the inner and outercurved lines are extended to said slot segment along the edge of theblade on which the slot segment is located, so as to form a convexcurved surface structure on the blade slot edge of each slot segment,and finally form a convex curved surface structure for the edge of theentire blade slot along the longitudinal direction of the blade. In thisway, the X-rays projected on the X-ray detector 112 will have equalwidth in the Z direction.

As described above, during operation of the X-ray tube 102, the focusthereof will shift as the temperature changes, thereby causing the X-raydetection area of the detector 112 to deviate from the initial X-raydetection area. Depending on the structure of the X-ray tube 102, theshift path of the focus of the X-ray tube can be a horizontal line, anoblique line, or other shapes. For simplicity, the following descriptionis based on the example where the shift path of the focus of the X-raytube is a horizontal line.

In the collimator 104 according to an embodiment of the presentinvention, when the focus of the X-ray tube 102 shifts, the collimatorcontroller 120 can control the rotating slot part 2041 in the collimator104 to rotate a certain angle to correct a route of the X-ray beampassing through the blade slot, so that the convex curved surfacestructure of the blade edge along the longitudinal direction of theblade can block some of the X-ray beams from the X-ray tube, therebycorrecting the X-ray beams projected onto the X-ray detector 112, suchthat the X-ray detection area of the X-ray detector 112 remainsunchanged when the focus of the X-ray tube 102 has changed. Thistracking process is referred to as Z-beam tracking

Next, reference will made to FIGS. 6A-6D to describe the Z-beam trackingprocess of an embodiment of the present invention in which thecollimator 104 is controlled by the collimator controller 120 in amanner such that the X-ray detection area of the X-ray detector 112remains unchanged when the focus the X-ray tube 102 shifts.

As shown in FIG. 6A, when the focus of the X-ray tube 102 is at thecenter of the focus shift range, the X-ray detection area of the X-raysprojected to the X-ray detector 112 via the slot of the selected bladeof the rotating slot part 2041 has a right edge point D2 and a left edgepoint D1, wherein focus shift range of the X-ray tube 102 depends on thestructure of the X-ray tube 102. In an exemplary cross-sectional view ofthe center of the blade slot along the thickness direction perpendicularto the longitudinal direction of the blade, a two-dimensional coordinatesystem YOZ is established using the blade rotation center as the originof coordinate. Based on the size, structure and the positionalrelationship of the various components of the CT system (including theX-ray tube 102, the collimator 104, the rotating slot part 2041 andblades of the collimator 104, and the X-ray detector 112), it ispossible to determine the horizontal position of the selected blade ofthe plurality of blades of the rotating slot part 2041, the positions ofthe focus of the X-ray tube 102 and the X-ray detector 112, and thepositions of the left and right edge points D1 and D2 in the X-raydetection region of the X-ray detector 112, in the established YOZdimensional coordinate system.

As shown in FIG. 6B, the right edge point F0 of the focus shift range ofthe X-ray tube 102 is selected as the initial reference position of theZ-beam tracking As X-ray beams are projected to the X-ray detector 112via the slot of the selected blade in the horizontal position, an X-raydetection area defined by the right edge point D2 and left edge point D1is formed. It will be appreciated by persons skilled in the art that itis also possible to select one of other positions of the focus shiftrange as the initial reference position of the Z-beam tracking, as longas the X-ray detection area required for CT scan formed on the X-raydetector 112 by the X-ray beams passing through the slot of the selectedblade are between the points D1 and D2.

When the focus of the X-ray tube 102 shifts due to temperature changeduring a CT scan, for example, a left shift p along the focus shift pathrelative to the initial reference position of the focus as shown in FIG.6C, a change will be caused to the X-ray detection area formed byprojection of X-ray beams onto the X-ray detector 112 via the bladeslot. The change of the X-ray detection area can be determined by anX-ray detection area offset monitoring unit provided on the X-raydetector 112.

In an embodiment, upon detection of a change of the X-ray detection areaon the X-ray detector 112 by the X-ray detection area offset monitoringunit as compared with the X-ray detection area when the focus of theX-ray tube 102 is at the initial reference position, the blade may be inthe horizontal position, which is compared to the position shown in FIG.6B, the angle B1 of the blade is zero. The blade may also be in otherlocations, for example, in a position as shown in FIG. 6C, where theangle of the blade is B1 which may be determined by an encoder 2042disposed in the collimator 104. As shown in FIG. 6C, the new X-raydetection area on the X-ray detector 112 has a right edge point D3 and aleft edge point D4, which correspond to two X-rays L12 and L22,respectively. The two X-rays represent two edges of the X-ray beamallowed to pass through the slot between the inner circular arc and theouter circular arc of the selected blade. The X-ray detection areaoffset monitoring unit may send the determined offset of the X-raydetection area, namely, the distance m between point D3 and point D2and/or the distance n between point D4 and point D1, to the collimatorcontroller 120.

The encoder 2042 disposed in collimator 104 can measure an angle ofrotation B1 of the selected blade around the rotation center O and sendthe measured angle B1 to the collimator controller 120. Based on thereceived angle B1 and the offset m and/or n of the X-ray detection area,as well as the positional relationships of the selected blade, therotating slot part 2041, the X-ray tube 102, and the X-ray detector 112in the two-dimensional coordinate system YOZ, the collimator controller120 can determine the shift p of the focus of the X-ray tube 102relative to the initial reference position.

Specifically, in an embodiment, the collimator controller 120 determinesthe position of the inner circular arc in the two-dimensional coordinatesystem YOZ based on the angle B1 measured by the encoder 2042 and theradius of rotation of the selected blade around the rotation center O.Then, based on the offset m of the X-ray detection area determined bythe X-ray detection area offset monitoring unit, as well as thepositional relationships of the selected blade, the rotating slot part2041, the X-ray tube 102, and the X-ray detector 112 in thetwo-dimensional coordinate system YOZ, the collimator controller 120determines a straight line L12 passing point D3 and tangent to the innercircular arc in the two-dimensional coordinate system YOZ, wherein thestraight line L12 represents the rightmost X ray of the X-ray beam whenthe focus of the X-ray tube 102 shifts from the right edge point F0 tothe new position F1, and the selected blade is at the rotation angle B1.The intersection point of the determined line L12 and the focus shiftpath of the X-ray tube 102 is the new position F1 of the shifted focusof the X-ray tube 102.

In an embodiment, the collimator controller 120 determines the positionof the outer circular arc in the two-dimensional coordinate system YOZbased on the rotation angle B1 of the selected blade, the radius ofrotation of the selected blade around the rotation center O, theposition of the inner circular arc and the positional relationship ofthe inner and outer circular arcs. Then, based on the offset ndetermined by the X-ray detection area offset monitoring unit, as wellas the positional relationships of the selected blade, the rotating slotpart 2041, the X-ray tube 102, and the X-ray detector 112 in thetwo-dimensional coordinate system YOZ, the collimator controller 120determines a straight line L22 passing point D4 and tangent to the outercircular arc in the two-dimensional coordinate system YOZ, wherein thestraight line L22 represents the leftmost X ray of the X-ray beam whenthe focus of the X-ray tube 102 shifts from the right edge point F0 tothe new position F1, and the selected blade is at the rotation angle B1.The intersection point of the determined line L22 and the focus shiftpath of the X-ray tube 102 is the new position F1 of the shifted focusof the X-ray tube 102.

In an embodiment, after the collimator controller 120 determines twofocus shift new positions F1 based on the straight lines L12 and L22 inthe two-dimensional coordinate system YOZ respectively, an average ofthe two new positions is used as the final focus shift new position F1.

The collimator controller 120 may, after determining the focus shift pof the X-ray tube 102 along the focus shift path and the rotation angleB1 of the selected blade, determine a rotation correction angle of theblade needed for eliminating of the offsets m and n of the X-raydetector region on the X-ray detector 112, and then cause the rotatingslot part 2041, driven by the motor drive system 2043, to rotate saidcorrection angle about the center of the rotation shaft 2042, so thatthe X-ray detection area formed by projection of X rays to the X-raydetector 112 via the slot of the selected blade remains unchanged as thefocus of the X-ray tube 102 shifts to a new location F1 along the focusshift path relative to the initial reference position F0, therebycompleting Z-beam tracking for focus shift of the X-ray tube 102.

Specifically, as shown in FIG. 6D, in an embodiment, after determiningthe focus shift p of the X-ray tube 102, the collimator controller 120can determine the position of the new position F1 of the focus in thetwo-dimensional coordinate system YOZ, and then determine a straightline L11 passing point F1 and point D2 in the two-dimensional coordinatesystem YOZ based on the determined new position F1 of the focus and theright edge point D2 of the initial X-ray detection area on the X-raydetector 112. When the X-ray detection area obtained on the X-raydetector 112 via the blade slot is remained unchanged as a result of theblade rotating a correction angle about the rotation center O after thefocus of the X-ray tube 102 has shifted a distance of p along the focusshift path, the inner circular arc of the slot of the selected blade istangent to the X-ray at line L11 in the two-dimensional coordinatesystem YOZ. Therefore, in the case that the line L11 is known, thecorrection angle B that the blade rotates around the rotation center Ocan be determined based on the positional relationship that the innercircular arc is tangent to line L11 and such known parameters as theradius of rotation of the blades.

In an embodiment, after determining the position of the new position F1of the focus in the two-dimensional coordinate system YOZ, thecollimator controller 120 then determines a straight line L21 passingpoint F1 and point D1 in the two-dimensional coordinate system YOZ basedon the determined new position F1 of the focus and the left edge pointD1 of the initial X-ray detection area on the X-ray detector 112. Whenthe X-ray detection area obtained on the X-ray detector 112 via theblade slot is remained unchanged as a result of the blade rotating acorrection angle about the rotation center O after the focus of theX-ray tube 102 has shifted a distance of p along the focus shift path,the outer circular arc of the slot of the selected blade is tangent tothe X-ray at line L21 in the two-dimensional coordinate system YOZ.Therefore, in the case that the line L21 is known, the correction angleB that the blade rotates around the rotation center O can be determinedbased on the positional relationship that the outer circular arc istangent to line L21, the positional relationship of the inner and outercircular arcs of the blade slot, and such known parameters as the radiusof rotation of the blade.

In an embodiment, the collimator controller 120 may, after determiningtwo correction angles B that the blade rotates around the rotationcenter O based on the straight lines L11 and L21 respectively, use anaverage of the two values as the final correction angle B for performingthe Z-beam tracking

Alternatively, the collimator controller 120 is further configured to,after completing a first Z-beam tracking for the focus shift of theX-ray tube 102, compare the offset m and/or n of the X-ray detectionarea determined in real time by the X-ray detection area monitoring unitwith a predetermined threshold. If the offset m and/or n determined inreal time do not exceed their respective thresholds, the Z-beam trackingis completed. If the offset m and/or n determined in real time exceedtheir respective thresholds, then the above procedure of Z-beam trackingmay be repeated until the latest offset m and/or n of the X-raydetection area do not exceed their respective thresholds.

In an embodiment, a plurality of focus shifts p of the X-ray tube 102along the focus shift path during a CT scan and a plurality ofcorresponding correction angles B (including the rotation direction)that the selected blade is required to rotate for achieving Z-beamtracking may be predetermined for each blade in the rotating slot part2041 based on simulation or actual measurements. The plurality of shiftsp and the corresponding correction angles B are stored in the form of atable in a memory within the collimator controller 120 or in an externalmemory coupled to the collimator controller 120 (not shown). When thefocus of the X-ray tube 102 shifts along the focus shift path due totemperature change during a CT scan of the subject 114, the collimatorcontroller 120 can determine the focus shift p of the X-ray tube basedon the offset m and/or n of the X-ray detection area determined by theX-ray detection area monitoring unit arranged on the X-ray detector 112,search in the memory for a blade rotation correction angle Bcorresponding to the focus shift p of the X-ray tube, and then cause theblade to rotate said correction angle around the rotation center underthe action of the motor drive system 2043, based on the blade rotationcorrection angle B found and the current angle B1 of the bladedetermined by the encoder 2042, thereby eliminating the offset m and/orn of the X-ray detection area on the X-ray detector 112 and achievingZ-beam tracking

If the collimator controller 120 fails to find a focus shift p of theX-ray tube in the memory, then it can search for two correction angles Bcorresponding to two focus shifts close to the focus shift p of theX-ray tube; based on the relationship between the focus shift p of theX-ray tube and the two adjacent focus shifts thereof, a final correctionangle B can be determined by performing an interpolation between the twocorrection angles B found. In an embodiment, if the collimatorcontroller 120 fails to find a focus shift p of the X-ray tube in thememory, a correction angle B corresponding to the focus shift closest tothe focus shift p of the X-ray tube can be searched for and used as thefinal correction angle B. In an embodiment, if the collimator controller120 fails to find a focus shift p of the X-ray tube in the memory, itcan search for two correction angles B corresponding to two focus shiftsclose to the focus shift p of the X-ray tube, and then use an average ofthe two correction angles B as the final correction angle B.

In an embodiment, a plurality of offsets m and/or n of the X-raydetection area on the X-ray detector 112 and a plurality ofcorresponding correction angles B (including the rotation direction)that the blade is required to rotate for achieving Z-beam tracking maybe predetermined based on simulation or actual measurements. Theplurality of offsets m and/or n of the X-ray detection area and thecorresponding correction angles B are stored in the form of a table in amemory within the collimator controller 120 or in an external memorycoupled to the collimator controller 120 (not shown). When the focus ofthe X-ray tube 102 shifts along the focus shift path due to temperaturechange during a CT scan of the subject 114, the collimator controller120 can search for a corresponding blade rotation correction angle B inthe memory based on the offset m and/or n of the X-ray detection areadetermined by the X-ray detection area monitoring unit arranged on theX-ray detector 112, and then cause the blade to rotate said correctionangle around the rotation center under the action of the motor drivesystem 2043, based on the blade rotation correction angle B found andthe current angle B1 of the blade determined by the encoder 2042,thereby eliminating the offset m and/or n of the X-ray detection area onthe X-ray detector 112 and achieving Z-beam tracking

If the collimator controller 120 fails to find an offset m and/or n ofthe X-ray detection area determined by the X-ray detection areamonitoring unit in the memory, then it can search for two correctionangles B corresponding to two offsets close to the offset m and/or n ofthe X-ray detection area; based on the relationship between the offset mand/or n of the X-ray detection area and the two close offsets thereof,a final correction angle B can be determined by performing aninterpolation between the two correction angles B found. In anembodiment, if the collimator controller 120 fails to find an offset mand/or n of the X-ray detection area determined by the X-ray detectionarea monitoring unit in the memory, a correction angle B correspondingto the offset closest to the offset m and/or n of the X-ray detectionarea can be searched for and used as the final correction angle B. In anembodiment, if the collimator controller 120 fails to find an offset mand/or n of the X-ray detection area determined by the X-ray detectionarea monitoring unit in the memory, it can search for two correctionangles B corresponding to two offsets close to the offset m and/or n ofthe X-ray detection area, and then use an average of the two correctionangles B as the final correction angle B.

Returning to FIG. 5, when the focus of the X-ray tube 102 shifts alongthe focus shift path due to temperature change, the collimatorcontroller 120 controls the selected blade in the collimator 104 torotate a correction angle about the rotation center to eliminate anoffset of the X-ray detection area formed by projection of X-rays to theX-ray detector 112 via the slot of the selected blade, so that the X-raydetection area is substantially restored to the initial position when nofocus shift takes place. As shown, after performing Z-beam tracking, theX-ray detection area A2 obtained on the X-ray detector 112 issubstantially consistent with the X-ray detection area A1 before focusshift. Simulation and actual measurements also show that after Z-beamtracking the X-ray detection area A2 obtained on the X-ray detector 112has extremely little difference as compared with the X-ray detectionarea A1 before focus shift. Accurate tracking is achieved at the D2 sideof the X-ray detection area on the X-ray detector 112, slight differenceis observed in the D1 side, and accurate tracking is achieved atleftmost and rightmost positions with respect to the angle shift of theX-ray tube.

The CT collimator according to an embodiment of the present inventionuses a single motor drive system to perform slot width selection andZ-beam tracking during a CT scan. As compared with conventional CTcollimators using at least two or more motor drive systems, the CTcollimator according to an embodiment of the present invention achievesa lower manufacturing cost. By using a single motor drive system todirectly drive the rotating slot part of the collimator, the presentcollimator requires no rails, ball screw or lead screw, and thus has asimpler structure than a conventional collimator, and hence higherreliability and better maintainability. In the CT collimator accordingto an embodiment of the present invention, according to needs of CTscans, the rotating slot part can be provided with a plurality of bladeshaving different slot widths. The edges of each blade slot along thelongitudinal direction of the blade have convex curved surfacestructures, so that when a focus shift of the radiation source along afocus shift path occurs as a result of temperature change, by rotatingthe selected blade about a rotation center eccentric to the blade acorrection angle corresponding to the focus shift, the radiation beamreaching the radiation detector via the blade slot is maintained at thesame region and same width as the circumstance when no focus shift takesplace. Therefore, the CT collimator and CT system according to anembodiment of the present invention eliminate the need of extraadjustment of the components such as the radiation detector when a focusshift of the radiation source occurs.

Although the present invention has been described with reference tospecific embodiments, it shall be understood that the present inventionis not limited to these specific embodiments. Skilled in the art willappreciate that various modifications, substitutions, changes and so onmay be made to the present invention. For example, in the aboveembodiments one step or component may be divided into multiple steps orcomponents; or, on the contrary, a plurality of steps or components inthe above embodiments may be realized in one step or one component. Allsuch variations should be within the scope of protection as long as theydo not depart from the spirit of the present invention. In addition, theterms as used in the present specification and claims are notlimitative, but descriptive. Moreover, according to actual needs, theentire or part of the features described in one specific embodiment canbe incorporated into another embodiment.

We claim:
 1. A lighting circuit, comprising: a first string of solidstate lighting devices in communication with a power source, the firststring of solid state lighting devices being connected in series witheach other; a second string of solid state light devices incommunication with the power source, the second string of solid statelight devices being connected in series with each other, the first andsecond string of solid state lighting devices being connected inparallel; and a current split circuit in communication with the firstand string of solid state lighting devices.
 2. The lighting circuitaccording to claim 1, wherein the current split circuit includes: afirst transistor connected in series with the first string of solidstate lighting devices; and, a second transistor in communication withthe first transistor and connected in series with the second string ofsolid state lighting devices, wherein the current split circuit areconfigured to divide a current substantially equally between the firststring of solid state lighting devices and the second string of solidstate lighting devices.
 3. The lighting circuit according to claim 2,further comprising: a third string of solid state lighting devices incommunication with the power source, the third string of solid statelighting devices being connected in series; and a fourth string of solidstate lighting devices in communication with the power source, thefourth string of solid state lighting devices being connected in series;and the current split circuit further comprising: a third transistor incommunication with the second transistor and connected in series withthe third string of solid state lighting devices; and, a fourthtransistor in communication with the third transistor and connected inseries with the third string of solid state lighting devices, thecurrent split circuit being configured to divide the currentsubstantially equally between the third string of solid state lightingdevices and the fourth string of solid state lighting devices.
 4. Thelighting circuit according to claim 3, wherein the current is dividedsubstantially equally between the first string of solid state lightingdevices, the second string of solid state lighting devices, the thirdstring of solid state lighting devices, and the fourth string of solidstate lighting devices.
 5. The lighting circuit according to claim 1,wherein the power source is a constant voltage generator.
 6. Thelighting circuit according to claim 1, wherein the power source is aconstant current generator.
 7. The lighting circuit according to claim1, wherein the first string of solid state lighting devices and thesecond string of solid state lighting devices each include multiplesolid state lights.
 8. The lighting circuit according to claim 1,wherein the solid state lighting devices are light emitting diodes. 9.The lighting circuit according to claim 2, wherein the first transistorand the second transistor form a mirror circuit that controls theillumination levels of the first string of solid state lighting devicesand the second string of solid state lighting devices to besubstantially uniform.
 10. The lighting circuit according to claim 2,wherein the solid state lighting devices are unbinned.
 11. The lightingcircuit according to claim 1, wherein the first string of solid statelighting devices and the second string of solid state lighting devicesare dimmable in at least one of a pulse width modulation mode and acontinuous mode.
 12. A lighting circuit, comprising: a plurality ofstrings of light emitting diodes connected to a power source, theplurality of strings of light emitting diodes being connected inparallel with each other; and a current split circuit connected to theplurality of strings of light emitting diodes, the current split circuitcomprising a plurality of transistors, including: a reference transistorconnected in series with a first of the plurality of strings of lightemitting diodes, and one or more copy transistors connected to thereference transistor and in series with one of the plurality of stringsof light emitting diodes, wherein the one or more copy transistorsdivides the current substantially equally between the plurality ofstrings of light emitting diodes.
 13. The lighting circuit according toclaim 12, wherein each of the plurality of strings of light emittingdiodes includes multiple light emitting diodes.
 14. The lighting circuitaccording to claim 12, wherein the power source is a constant voltagegenerator.
 15. The lighting circuit according to claim 12, wherein thepower source is a constant current generator.
 16. The lighting circuitaccording to claim 12, wherein the current split circuit controls theillumination levels of the plurality of strings of light emitting diodesto be substantially uniform.
 17. A lighting method, comprising:providing a power source; providing a plurality of strings of lightemitting diodes in communication with the power source, the plurality ofstrings of light emitting diodes being connected in parallel with eachother; providing a current split circuit in communication with theplurality of strings of light emitting diodes, the current split circuithaving a plurality of transistors that form a mirror circuit; anddividing the current equally between each of the plurality of strings oflight emitting diodes such that the light emitting diodes areilluminated at substantially the same level.
 18. The lighting methodaccording to claim 17, further comprising dimming the plurality ofstrings of light emitting diodes.
 19. The lighting method according toclaim 18, wherein the plurality of strings of light emitting diodes aredimmable in pulse width modulation mode.
 20. The lighting methodaccording to claim 18, wherein the plurality of strings of lightemitting diodes are dimmable in continuous mode.